U.S. patent application number 13/446808 was filed with the patent office on 2012-08-09 for non-invasive system and method for measuring an analyte in the body.
This patent application is currently assigned to BAYER HEALTHCARE LLC. Invention is credited to Mihailo V. Rebec.
Application Number | 20120203085 13/446808 |
Document ID | / |
Family ID | 37056467 |
Filed Date | 2012-08-09 |
United States Patent
Application |
20120203085 |
Kind Code |
A1 |
Rebec; Mihailo V. |
August 9, 2012 |
NON-INVASIVE SYSTEM AND METHOD FOR MEASURING AN ANALYTE IN THE
BODY
Abstract
A system for determining an analyte concentration in a fluid
sample (e.g., glucose) comprises a light source, a detector, and a
central processing unit. The detector is adapted to receive
spectral information corresponding to light returned from the fluid
sample being analyzed and to convert the received spectral
information into an electrical signal indicative of the received
spectral information. The central processing unit is adapted to
compare the electrical signal to an algorithm built upon
correlation with the analyte in body fluid. The algorithm is
adapted to convert the received spectral information into the
analyte concentration in body fluid. Spectral information is
delivered from the central processing unit to the light source and
used to vary the intensity and timing of the light to improve the
accuracy of conversion into analyte concentration.
Inventors: |
Rebec; Mihailo V.; (Bristol,
IN) |
Assignee: |
BAYER HEALTHCARE LLC
Tarrytown
NY
|
Family ID: |
37056467 |
Appl. No.: |
13/446808 |
Filed: |
April 13, 2012 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11918537 |
Oct 15, 2007 |
8180422 |
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PCT/US2006/014152 |
Apr 13, 2006 |
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13446808 |
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60672167 |
Apr 15, 2005 |
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Current U.S.
Class: |
600/310 ;
356/436; 356/445 |
Current CPC
Class: |
G01J 3/433 20130101;
G01J 3/10 20130101; A61B 5/1495 20130101; G01J 2003/2866 20130101;
G01N 2021/3144 20130101; A61B 5/1455 20130101; G01J 3/0262
20130101; G01J 3/0218 20130101; A61B 5/14532 20130101; G01J 3/28
20130101; G01N 21/35 20130101; A61B 5/726 20130101; G01J 3/02
20130101; G01J 3/1256 20130101; G01J 3/0272 20130101; G01N
2021/3185 20130101 |
Class at
Publication: |
600/310 ;
356/436; 356/445 |
International
Class: |
A61B 5/00 20060101
A61B005/00; G01N 21/55 20060101 G01N021/55; G01N 21/59 20060101
G01N021/59 |
Claims
1. A system for determining the concentration of an analyte in a
fluid sample, the system comprising: a light source delivering
light within a predetermined wavelength range; a detector adapted
to receive spectral information corresponding to light returned
from said fluid sample and to convert the received spectral
information into an electrical signal indicative of the received
spectral information; and a central processing unit adapted to
compare the electrical signal to an algorithm built upon
correlation with the analyte in the body fluid, the algorithm
adapted to convert the received spectral information into the
concentration of said analyte in said fluid sample, the central
processing unit controlling the light source and varying the
intensity and timing of the delivery of said light within said
predetermined wavelength range to improve the accuracy of
conversion of the received spectral information into concentration
of said analyte in said fluid sample.
2. The system of claim 1, wherein said light source is a series of
beams of monochromatic light that scan across the predetermined
wavelength range.
3. The system of claim 2, further comprising a reference detector
adapted to receive a portion of said series of beams of
monochromatic light and to convert the received light into a
reference electrical signal.
4.-12. (canceled)
13. The system of claim 1, wherein said light source delivers to
said sample predetermined wavelengths of light at predetermined
intensities and said spectral information returned from said sample
is processed to provide spectral information at wavelengths where
said analyte is more readily distinguished from interfering
substances.
14. The system of claim 1, wherein said light source contains
information that is used to correct for the effect on the light
spectra of the sample, light delivery and collection systems, and
detector.
15. The system of claim 1, wherein said light source contains
information that corrects for changes in the analyte-related
spectrum by the sample, light delivery and collection methods, and
detector distortions.
16. The system of claim 1, wherein said light source contains
concentration-related spectra that correct for non-linear responses
of the analyte.
17. A method for determining the concentration of an analyte in a
fluid sample, the method comprising the acts of: delivering light
within a predetermined wavelength range from a light source;
receiving spectral information corresponding to light returned from
said fluid sample; converting the received spectral information
into an electrical signal indicative of the received spectral
information; comparing the electrical signal to an algorithm built
upon correlation with the analyte in the fluid sample; and
converting the received spectral information into the concentration
of said analyte in said fluid sample via a central processing unit,
the central processing unit controlling the light source and
varying the intensity and timing of the delivery of said light
within said predetermined wavelength range to improve the accuracy
of conversion of the received spectral information into
concentration of said analyte in said fluid sample.
18-50. (canceled)
51. A method for determining the concentration of an analyte in
body fluid, the method comprising the acts of: delivering
substantially monochromatic light using an infrared light source
sequentially across a predetermined wavelength range; contacting
body tissue using a body tissue interface; delivering light from
said infrared light source to the contacted body tissue; receiving
light reflected from the body fluid; converting the received
reflected light into an electrical signal indicative of the
received reflected light; comparing the electrical signal to an
algorithm built upon correlation with the analyte in the body fluid
via a central processing unit; and converting the received spectral
information into the concentration of the analyte in said body
fluid, wherein the central processing unit controls said infrared
light source and varies the intensity and timing of the delivery of
said monochromatic light with the predetermined wavelength range to
improve the accuracy of conversion of the received spectral
information into concentration of said analyte in said fluid.
52. The method of claim 51 further including disposing an index
matching medium disposed between the body tissue interface and the
received body tissue, wherein the infrared light delivered to the
body tissue and reflected by the body tissue passes through the
index matching medium.
53. The method of claim 51, wherein the infrared light has a
wavelength ranging between approximately 1400 nanometers and
approximately 2500 nanometers.
54. The method of claim 51, wherein the intensity of said
monochromatic light is uniform over said predetermined wavelength
range.
55. The method of claim 51, wherein the intensity of said
monochromatic light is varied across said predetermined wavelength
range to provide spectral information received from said sample
having uniform intensity across said predetermined wavelength
range.
56. The method of claim 51, wherein said monochromatic light
contains information that is used to correct for the effect on the
light spectra of the sample, light delivery and collections systems
and detector distortions.
57. The method of claim 51, wherein said light source contains
concentration-related spectra that correct for non-linear responses
of the analyte.
Description
FIELD OF THE INVENTION
[0001] The present invention relates generally to systems for the
determination of analytes by their interaction with infrared,
visible, or ultraviolet radiation. In some important applications,
analytes in body fluids are measured, (e.g., non-invasive measuring
of glucose in the body).
BACKGROUND OF THE INVENTION
[0002] Those who have irregular blood glucose concentration levels
are medically required to regularly self-monitor their blood
glucose concentration level. An irregular blood glucose level can
be brought on by a variety of reasons including illness such as
diabetes. The purpose of monitoring the blood glucose concentration
level is to determine the blood glucose concentration level and
then to take corrective action, based upon whether the level is too
high or too low, to bring the level back within a normal range. The
failure to take corrective action can have serious implications.
When blood glucose levels drop too low--a condition known as
hypoglycemia--a person can become nervous, shaky, and confused.
Their judgment may become impaired and they may eventually pass
out. A person can also become very ill if their blood glucose level
becomes too high--a condition known as hyperglycemia. Both
conditions, hypoglycemia and hyperglycemia, are potentially
life-threatening emergencies.
[0003] Common methods for monitoring a person's blood glucose level
are invasive in nature. Typically, to check the blood glucose
level, a drop of blood is obtained from the fingertip using a
lancing device. The blood drop is produced on the fingertip and the
blood is harvested using a test sensor which is inserted into a
testing unit. The test sensor draws the blood to the inside of the
test unit which then determines the concentration of glucose in the
blood.
[0004] One problem associated with this type of analysis is that
there is a certain amount of pain associated with the lancing of a
finger tip. Diabetics must regularly self-test themselves several
times per day. Each test requires a separate lancing, each of which
involves an instance of pain for the user. Further, each lancing
creates a laceration in the users skin which take time to heal and
are susceptible to infection just like any other wound.
[0005] Other techniques for analyzing a person's blood glucose
level are noninvasive in nature. Commonly, such techniques
interpret the spectral information associated with light that has
been transmitted through or reflected from a person's skin. An
advantage of this type of noninvasive analysis is that there is no
associated pain or laceration of the skin. However, thus far, such
techniques have proven unreliable because many techniques fail to
recognize the many issues that impact the analysis. For example,
many noninvasive reflectance and transmission based systems do not
account for the fact that the obtained spectral data contains
glucose information from the portion of body tissue being analyzed
as a whole, and is not limited to blood glucose. Other techniques
do not account for irregularities in the spectral signal of the
analyte due instrumental drift, temperature changes in the tissue
under analysis, spectral characteristics of the tissue that change
due to pressure changes, etc. that can occur during the analysis or
between analyses. These irregularities can impact the quality of
the calibration model or the algorithms that are used to determine
the analyte concentrations from the noninvasively collected
spectral data. The spectral data that has these irregularities
cannot be used by the algorithms to determine the analyte
concentrations.
[0006] Accordingly, there exists a need for a reliable noninvasive
system for the determination of analytes in body fluids.
[0007] Near infrared radiation has been applied non-invasively in
attempts to identify the glucose content of a patient's blood.
However, non-invasive methods subject to the infrared radiation
areas of the body that contain blood vessels, but other fluids
containing glucose are present. A person's skin contains glucose in
the extracellular fluid, which includes plasma and interstitial
fluid. Since measurements of glucose by non-invasive methods are
made in the dermis, they primarily determine the glucose in the
extracellular fluid, plus some glucose in blood contained in
capillaries in the skin. What is wanted is a correlation with the
glucose content of blood, typically a small amount in the general
range of 50 to 450 mg/dL. Now, it will be evident that if
absorption of infrared radiation at specific wavelengths that are
associated with glucose could be detected and measured, then the
desired information will have been obtained. In practice, the
presence of water and other materials that absorb infrared
radiation make it difficult to measure the amount of glucose in the
blood that is present and exposed to the infrared radiation. Some
research has been directed to comparing the absorption of infrared
radiation at certain wavelengths with a reference beam that has not
been directed to the skin of a subject. More commonly, attempts
have been made to correlate the response of a subject to a
broadband of infrared radiation with measurements made by reliable
methods of determining the glucose content of blood obtained by
invasive methods.
[0008] In some patents including U.S. Pat. Nos. 5,435,309 and
5,830,132, methods are described in which, rather than applying a
broadband of radiation or pre-selected wavelengths, a band of
infrared radiation is scanned using acousto-optic tunable filters
(AOTF). These solid state devices permit rapid scanning of a band
of radiation without using filters or moving parts. The response of
the subject to the radiation is detected and correlated using
techniques familiar to those skilled in the art such as, for
example, partial least squares (PLS) and principal component
analysis (PCA).
[0009] In co-pending U.S. patent application Ser. No. 10/361,895
published as U.S. 2004/0092804A1, an improved method of measuring
glucose non-invasively that employs AOTF was disclosed. In addition
to an algorithm developed to correlate the spectral information
with direct measurements of glucose in a subject's blood, the
system employed several unique features that improved accuracy and
consistency. Those features included a clamping device for assuring
good contact with body tissue and which provided precise
temperature and pressure control at the point of measurement. A
unique attachment clamping device, including sapphire rods, termed
an optoid by the inventors, were provided to direct radiation into
the measurement region and transmit light leaving the region to the
radiator detector. The device represented an advance in the art,
but further improvement was sought by the present inventor.
[0010] It will be evident from the above discussion that obtaining
accurate measurements of small amounts of glucose in blood by
non-invasive methods is difficult since the concentration of
glucose is small relative to other materials in the sample area and
its response to infrared radiation occurs in regions in which other
materials in higher concentrations also respond. At least two
important problems are involved. First, much of the incident
radiation is absorbed or scattered and the amount actually received
by the detector is small. Thus, improving the signal-to-noise ratio
is important. Second, water is present in large amounts relative to
glucose and interferes with accurate measurement of glucose. This
is especially a problem with instruments that employ a wide band of
infrared radiation such as scanning and diode array instruments. As
discussed above, instruments using AOTF scan a predetermined
radiation band. This makes possible adjusting the power of the
monochromatic light provided by the AOTF device so that the signal
received at pre-selected wavelengths is maximized across the entire
spectral region. Due to the different absorbency and scattering
characteristics of the skin in the infrared region, the spectrum
collected from the skin can have orders of magnitude differences in
intensity. The limitations of most systems are that they are not
able to maximize the information quality across such a divergent
spectral region. Improvement of the signal-to-noise ration would be
advantageous. Varying skin characteristics that affect scattering
and absorbance of infrared radiation can be accounted for and then
the signal-to-noise ratio could be improved. Another improvement in
an AOTF device would provide feedback to adjust the power and the
scanning time to provide the most accurate results. Further
improvement could be obtained by programming the AOTF to change the
amplitude of the radiation in specific regions of the spectrum that
are obtained from an interaction with a known glucose
concentration. The information so obtained would help to
characterize the scattering, absorbance, and interference effects
associated with a pure glucose sample.
[0011] The present inventor has found that an improved non-invasive
glucose-measuring instrument can be made employing the
above-described principles. Such an improved instrument will be
described in detail below. Furthermore, the principles employed in
the glucose-measuring instrument may be applied more generally to
measuring analytes in may other instances.
SUMMARY OF THE INVENTION
[0012] In its more general aspects, the invention includes an
instrument that supplies a source of infrared, visible, or
ultraviolet light to a sample believed to contain an analyte and
that retrieves returned light reflected from or transmitted through
the sample and determines the amount of the analyte by the
absorption of the light. The non-invasive system for measuring
glucose in the fluid in body tissue is one example. The light
source may be an AOTF, laser diode array, a filtered broad band
light source, or other sources that provide light in predetermined
wavelength regions to a sample being inspected. A central
processing unit will control the supply of light to the sample and
its measurement upon its return to a detector. The central
processing unit will provide one or more sets of light spectra to
improve accuracy of the conversion of the received spectral
information into concentration of the analyte in the sample. Light
spectra may include one or more of the following, preferably in
sequence. [0013] a source of light in which each wavelength segment
has equal intensity over the wavelength range [0014] a source of
light in which the intensity of each wavelength segment is adjusted
to provide returned light having equal intensity throughout the
wavelength range [0015] a source of light in which a sample is
exposed to light of predetermined wavelengths for varying times
[0016] a source of light in which a sample is exposed to light only
at wavelengths determined to have the least signal-to-noise ratio.
[0017] a source of light in which a sample is exposed to light at
wavelengths determined to have a high signal-to-noise ratio, but at
which significant information regarding the analyte is believed to
be present. [0018] a source of light that contains information that
corrects for changes in the analyte-related spectrum by the sample,
light delivery and collection methods such as fibers or lenses, and
the detector distortions. [0019] a source of light containing
concentration-related spectra that correct for non-linear responses
of the analyte.
[0020] The results obtained with those light spectra that are
intended to emphasize certain regions of returned light may also be
achieved by using a uniform intensity light source and processing
the returning light.
[0021] In one embodiment, the invention includes a system for
determining the concentration of an analyte in the fluids in body
tissue (e.g., glucose in extracellular fluids) that comprises an
infrared light source, a monochromatic device (e.g., an AOTF), a
body tissue interface, a detector, and a central processing unit.
The body tissue interface is adapted to contact body tissue and to
deliver light from the monochromatic light source across a
predetermined wavelength range to the contacted body tissue. The
detector is adapted to receive spectral information corresponding
to infrared light transmitted through or reflected from the portion
of body tissue being analyzed and to convert the received spectral
information into an electrical signal indicative of the received
spectral information. The central processing unit is adapted to
compare the electrical signal to an algorithm built upon
correlation with the analyte in body fluid, the algorithm adapted
to convert the received spectral information into the concentration
of the analyte in body fluids.
[0022] In one embodiment of the invention, the light is modulated
to correspond with a spectrum obtained by interaction of the light
with a pure glucose sample.
BRIEF DESCRIPTION OF THE FIGURES
[0023] FIG. 1 is a diagram of a transmission-based system for
determining analytes in body fluids.
[0024] FIG. 2 is a plot of the absorbency of transmitted light
versus wavelength of the transmitted light according to one
embodiment of the transmission-based system illustrated in FIG.
1.
[0025] FIG. 3 is a flow chart depicting a method for building a
glucose calibration algorithm.
[0026] FIG. 4a is a diagram of the contact with the body of a
reflectance-based system for determining analytes in body
fluids.
[0027] FIG. 4b is a cross-sectional view taken generally along line
4b-4b of FIG. 4a.
[0028] FIG. 5 is a plot of the absorbency of reflection light
versus wavelength of the reflected light according to one
embodiment of the reflected-based system illustrated in FIG.
4a.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0029] In the discussion that follows, application of the general
principles of the invention will be discussed with particular
reference to the non-invasive measurement of the glucose content of
body fluids, a method of commercial importance. Similarly,
application of the methods of the invention could be applied to
analyzing other analytes in the body fluids, such as cholesterol,
hemoglobin, creatinine, alcohol, bilirubin, albumin, total
proteins, and globulins. However, it should be understood that the
invention is not limited to that specific application, but it can
be applied in many other situations where analytes are determined
by their interaction with infrared, visible, or ultraviolet light.
For example, measuring glucose or other sugar molecules in
fermentation processes.
[0030] Determining the glucose content of blood is commonly used to
monitor the need for medication or dietary changes in diabetic
patients. Non-invasive methods of measuring glucose have been of
interest, since they avoid the need for sampling blood. Thus, in
one important embodiment, the invention has application in
non-invasive methods for measuring glucose in body tissue and in
which light is either passed through or reflected from body
tissue.
Transmission-Based System
[0031] Referring to FIG. 1, a transmission-based non-invasive
system 10 for the determination of analytes in body fluids is
functionally illustrated. The system 10 uses near infrared light
transmitted through a piece of skin, such as the "web" of skin
between a patient's index finger and thumb. Conventionally, a
patient's glucose level measured in this way is referred to as
their blood-glucose level. However, the measurement is principally
made of glucose in the interstitial fluid and inter-cellular
material. Accordingly, the present inventor prefers to refer to a
patient's glucose level, which can be correlated with a patient's
blood glucose level, as will be seen.
[0032] Human skin consists of approximately sixty percent
extracellular material and 40% intracellular material. The
extracellular material comprises approximately 30% plasma (blood)
and about 70% interstitial fluid ("ISF"). Therefore, when examining
the spectral characteristics of glucose from infrared light that is
transmitted though a patient's skin, all the glucose in that
portion of skin is being measured, rather than only the glucose in
a patient's blood. The largest portion of the transmitted light is
made up of light transmitted though ISF, and not blood plasma.
Conversely, in an invasive setting where a 10 .mu.l drop of blood
is obtained on a patient's finger tip, for example, the measured
glucose concentration primarily represents the concentration of
glucose in that patient's blood, rather than in other fluids.
[0033] The system 10 is used to obtain transmitted spectral
information from a patient for correlation with invasive
measurements from the same patient. For example, the system 10 is
used in a test wherein the glucose concentration of the test
subject is modulated to a plurality of different concentration
levels. One such test is a glucose clamping test where the glucose
level of the test subject is raised and lowered to various levels
over the duration of the test. According to one embodiment, the
glucose clamping test is designed to bring the test subject's
glucose level to six plateau regions that range in concentration
from 50 to 300 mg/dL. Each plateau is separated by about 50 mg/dL
so that each region can be clearly distinguished. ISF and plasma
samples are collected throughout the duration of the clamping test.
The samples are collected every five minutes and are analyzed for
glucose content. This measurement is used to adjust the infusion of
glucose or insulin to maintain the glucose concentration of the
plasma for about twenty-five minutes at a particular targeted
plateau region. The spectral data obtained over the course of the
test are compared to the actual glucose levels (determined using
invasive techniques) obtained during the test. From this data, a
calibration algorithm is built to predict the actual glucose level
of the patient based on the spectral characteristics of light
transmitted through that patient's skin. This calibration algorithm
can then be incorporated into a handheld version of the system 10
illustrated in FIG. 1.
[0034] Such a handheld instrument would enable a user to
noninvasively monitor the user's glucose concentration level. The
user would contact the user's skin with the instrument to obtain
spectral information from the user's skin. The instrument would
then provide the user with a reading of the user's glucose
concentration level a short time later. Sources of monochromatic
infrared light include, for example, a Tungsten-Halogen light and
an acoustic-optic tunable filter (AOTF). Referring to FIG. 1, an
acoustic-optic tunable filter ("AOTF") spectrometer is shown
generally by dashed line 12. The AOTF spectrometer 12 outputs a
monochromatic, modulated beam of light 14 into a fiber optic cable
16 via a lens 18. The AOTF spectrometer 12 includes a light source
20. According to one embodiment, the light source 20 is a
Tungsten-Halogen light source, which is a low-cost, stable light
source that outputs a good amount of light (e.g., 250 watts).
Alternative light sources include light emitting diodes ("LED"),
doped fibers including uranium doped fibers, and laser diodes. The
light source produces a beam of light 22 in the near-infrared
region (i.e., having a wavelength ranging 750-2500 nanometers).
This light is used to provide a series of monochromatic beams that
scan across the beam width.
[0035] Generally, the AOTF spectrometer 12 functions as an
electronically tunable spectral band-pass filter to output the
monochromatic beam of light 14 having wavelengths within a desired
range. The AOTF 12 is a solid state electro-optical device that
consists of a crystal 19 in which acoustic (vibrational) waves, at
radio frequencies ("RF") are used to separate a single wavelength
of light from the broadband light source. The wavelength selection
is a function of the frequency of the RF applied to the crystal 19.
The crystal 19 used in AOTF devices can be made from a number of
compounds. According to one embodiment of the present invention,
the crystal comprises Tellurium Dioxide (TeO.sub.2). TeO.sub.2
crystals providing good results for use with light in the 1200 to
3000 nm spectral region. According to one embodiment, the crystal
19 is used in a non-collinear configuration, wherein the acoustic
and optical waves (paths) through the crystal 19 are at very
different angles from each other. Alternatively, collinear
configured AOTF devices may be used. A transducer (not shown) is
bonded to one side of the crystal. This transducer emits vibrations
(acoustic waves) when RF is applied to the transducer.
[0036] As the acoustic waves pass from the transducer to the
crystal 19, the crystal 19 alternately compresses and relaxes
resulting in a refractive index variation that acts like a
transmission diffraction grating. Unlike a classical grating,
however, the crystal only diffracts one specific wavelength of
light so it acts like a filter more than as a diffraction grating.
The wavelength of the light that is diffracted is determined by a
phase matching condition based on the birefringence of the
TeO.sub.2 crystal and the velocity and frequency of the acoustical
wave and as well as parameters specific to the design of the AOTF.
The wavelength that is selected is varied by simply changing the
frequency of the applied RF. The diffracted light is directed into
two first order beams that we call the positive and negative beams.
The rest of the undiffracted light is passed through as
undiffracted zero (0) order beam. The positive and negative beams
are orthogonally polarized. The positive beam is delivered to the
optoid as described below and the negative beam is used as a
reference beam to correct for variations in the intensity of the
light source or the efficiency of the AOTF as described below.
Alternatively, the positive beam could be split and a portion used
as a reference, while the remainder is sent to the optoid.
[0037] According to one embodiment, the beam of light 14 output by
the AOTF spectrometer has a resolution or bandwidth of from about
four to about ten nanometers ("nm"). This bandwidth is swept (back
and forth) across a wavelength range of about 1400 to 2500
nanometers. Put another way, the AOTF spectrometer 12 outputs light
having a wavelength continuously ranging between 1400 and 2500 nm
and has a resolution of from about 4 to about 10 nm. The timing of
the sweep can range from several milliseconds to several seconds. A
suitable AOTF spectrometer is available from Crystal Technologies,
Inc. of Palo Alto, Calif. as AOTF Model 2536-01. The AOTF
spectrometer includes a RF driver, a mixer, and a low frequency
oscillator (not shown) for modulating the monochromatic beam of
light 14 at approximately 20,000 Hz. Although the light can be
modulated at this frequency, others can be used to provide
comparative results used to refine the corrections to the light
spectra obtained.
[0038] A voltage control oscillator (not shown) provides the
control of the RF frequency. Separate circuitry (not shown) is used
for modulation and power control, which range from 0 to about 0.5
watts. A suitable voltage control oscillator is available from the
Inrad Corporation, Northvale, N.J., Model DVCO-075A010. The power
is delivered to an acoustical transducer that creates an acoustical
wave that changes the characteristic of a birefringence crystal 19
so that full spectrum light is separated to wavelengths associated
with a particular frequency and the rest of the light passes
through as zero order light.
[0039] The crystal 19 of the AOTF spectrometer 12 splits the beam
of light 22 into the first beam 14 and a second beam 23. The second
beam of light 23 is directed to a reference detector 24 for
measuring/recording the light input to the skin. Additionally, the
reference detector 24 measures/records the light 23 for instrument
drift associated with the light source and AOTF that can occur over
time due to the length of operating time and change in temperature
of the instrument over that time period.
[0040] The light 14 output by the AOTF spectrometer 12 is directed
into the lens 18 that reduces the diameter of the beam of light and
focuses the beam of light 14 into an end of the fiber optic cable
16. The lens 18 effectively couples the AOTF spectrometer 12 to the
fiber optic cable 16. The fiber optic cable 16 is a low OH (i.e.,
preferably about 0.3 parts per million or below (of water in
silica) fiber optic cable which has low attenuation over the length
of the cable. The higher the OH content, the greater the intrinsic
absorbance of the fiber itself especially in the wavelength region
above 2100 nm. According to another embodiment, the fiber optic
cable has an OH of less than about 0.12 ppm. The quality of light
input to the fiber optic cable 16 is substantially maintained when
delivered to a patient's skin at an opposite end 33 of the fiber
optic cable 16. The output end 33 of the fiber optic cable 16
connects to a device the inventor has termed an optoid 34.
Generally, the optoid 34 consists of the hardware that interfaces
with the patient's skin. The optoid 34 includes a first plate 46
and a second plate 48, which are slideably clamped onto the tissue
being analyzed, such as the web of skin 52 ("the web 52") of a
patient's hand between the index finger and thumb. The optoid 34
includes a sapphire rod 42 that delivers light from the fiber optic
cable 16 to the web 52. The sapphire rod 42, having a diameter of
about three millimeters in one embodiment, increases the diameter
of the beam of light input to the web 52. Fiber optic cables are
typically limited in diameter to about two millimeters. The larger
diameter of the sapphire rod 42 provides an effective means of
coupling light that can be up to 3 mm in beam diameter to be
delivered to the skin. Delivering a wider beam of light (e.g., the
3 mm of the sapphire rod as opposed to the 2 mm diameter of the
fiber optic cable) covers a larger area of skin which limits the
impact of small irregularities in skin properties. The sapphire rod
42 is flush with the interior surface of the first plate 46.
[0041] The light that is directed into the web 52 via the sapphire
rod 42 is transmitted through the web 52 and into a second sapphire
rod 54 (also 3 mm in diameter) disposed within the second plate 48.
The light passing through the web 52 is generally represented by
arrows 56. The amount of light transmitted through the web 52 is
very low. Typically, less than about two percent of the light
exiting the first sapphire rod 42 enters into the second sapphire
rod 54. The light transmitted through the web 52 is directed by the
second sapphire rod 54 into a detector 58. According to one
embodiment of the present invention, the detector 58 is an extended
Indium Gallium Arsenate ("InGaAs") detector having a circular
active surface of three millimeters in diameter and provides a
response across the 1300 to 2500 nm spectral region. Such a
detector is commercially available from the Hamamatsu Corporation.
According to one embodiment of the present invention, the reference
detector 24 and the detector 58 are the same type of detector.
Examples of other types of detectors that can be used in
alternative embodiments of the present invention include Indium
Arsenide ("InAs"), Indium Selenide ("InSe"), Lead Sulfide ("PbS"),
Mercury-Cadmium-Telluride ("MCT"), and DTG detectors. Other types
of detectors can be used depending on the desired region of the
spectrum to be analyzed for determining the glucose concentration
level. As is discussed in greater detail below in connection with
FIG. 2, glucose exhibits unique spectral characteristics in the
about 1450-1850 nm and the about 2200-2500 nm spectral range. The
detector 58 generates an electrical signal indicative of the
detected transmitted light, which is processed as is described in
detail below.
[0042] In addition to providing a mechanism for transmitting light
through the web 52, the optoid 34 performs other mechanical
functions. First, the moveable first and second plates 46,48 (also
referred to as "jaws") provide pressure to compress the web 52 to
maintain a consistent optical path through the web 52. Compressing
the web 52 brings a greater consistency to the testing process.
According to one embodiment, the plates 46, 48 compress the tissue
approximately six percent from its original thickness. Compressing
the tissue also creates a flush interface between the web of skin
and the plates 46,48 by eliminating air gaps between the web 52 and
plates 46,48 so that the light transmitted from the first sapphire
rod 42 directly enters the web 52. The optoid 34 includes a load
cell 56 to measure the contact pressure on the web of skin 52.
During the analysis, pressure measurements and temperature
measurements are obtained so that irregularities associated with
changes in pressure or temperature can be accounted for as
discussed in greater detail below. Also, compressing the skin
reduces the "noise" created by pulsing of the blood through the
region being analyzed.
[0043] Second, each of the plates 46,48 includes thermal-electric
heaters (not shown) that heat the web 52 to a uniform temperature.
According to one embodiment of the present invention, the
thermal-electric heaters heat the web to about 100.degree.
F..+-.0.1.degree. F. The thermal-electric heaters, which are
incorporated into each of the plates, are able to provide very
accurate temperature control. Typically, the temperature
differential between the surface of skin and the interior ranges
between 5-7.degree. F. Heating the skin to a substantially uniform
level significantly reduces scattering of the light transmitted
through the skin due to temperature gradients resulting in a more
consistent analysis. Additionally, heating the skin to about
100.degree. F. expands the capillaries and increases the amount of
blood in the capillaries by approximately 300%, thus bringing more
glucose into the area of analysis.
[0044] As discussed above, the AOTF 12 modulates the wavelength of
the beam of light 14, which causes the beam of light transmitted
through the skin via the optoid 34 to be modulated. The modulation
aids in resolving some of the issues associated with instrument
drift that can affect the quality of the spectral information. The
modulated, transmitted light is received by the detector 58 and the
modulated transmitted light strikes the active material of the
detector 58 and is converted by the detector into an electrical
current indicative of the light received. According to one
embodiment, the electrical signal generated by the detector 58 is
amplified by an amplifier (not shown) and sent to a lock-in
amplifier 70, which demodulates the signal. A suitable lock-in
amplifier 70 is available from Stanford Research Instruments, Model
SR 810 DSP, according to one embodiment of the present invention.
Alternatively still, the lock-in amplifier is integrated into an
integrated circuit board comprising the described electrical
hardware of the present invention.
[0045] An analog-to-digital converter 72 then digitizes the
demodulated signal. According to one embodiment of the present
invention, the analog-to-digital converter is a sixteen-bit
converter available from National Instruments Corporation of
Austin, Tex. It is contemplated that other analog-to-digital
converters may be used. Alternatively, digitization is incorporated
into an integrated circuit board comprising the described
electrical hardware of the present invention. In other alternative
embodiments, the digitization is at an 18 bit or higher bit
rate.
[0046] The spectral data are optionally passed through a first
filter 74 to remove high frequency noise and then a second filter
76 to remove slow drifting that occurs due to gradual changes in
the patient's skin over the course of the analysis, or drift
observed in the instrument or the optical fibers. Filtering the
signal in this manner improves the overall signal-to-noise
ratio.
[0047] The signal is then passed on to a central processing unit
("CPU") 78. The CPU 78 averages the received signal, resulting in
approximately 500 data sets taken each minute over approximately
500 minutes. The data are saved with a tracking of the wavelength
of the light input to the optoid 34. The spectral signal is also
stored along with the time associated skin temperature, room
temperature, pressure applied to the skin during the measurement,
and blood pressure measurements. This information is useful in
determining whether any irregularities in the spectral signal are
the result of changes in these types of factors and not the result
of changes in the glucose concentration. The data are then
processed to improve the signal-to-noise quality of the data and to
remove artifact effects that can corrupt the quality of the
spectral data. According to alternative embodiments of the present
invention, the processing to improve the signal-to-noise ratio can
be accomplished in a variety of manners. For example, in one
alternative embodiment, the signal-to-noise quality of the signal
is improved by using Wavelet transforms to remove high frequency
noise and low frequency baseline drift type of noise (i.e.,
irrelevant spectral variations that are determined by the
information entropy corresponding to glucose levels). According to
another alternative embodiment, the signal-to-noise quality is
improved using such classical methods such as Savitsky-Golay
multipoint smoothing. In other embodiments, first derivative
analysis can be used to deal with baseline issues such as baseline
drift type of noise.
[0048] Additionally, the noise in the signal is improved by
removing spectral information that is not related to the relevant
glucose information according to alternative embodiments of the
present invention. This is accomplished by the application of a
Genetic Algorithm for selecting wavelength regions that are the
most related to the glucose changes and removing others that are
not. This process results in the development of robust calibration
algorithms that significantly reduce overfitting issues. In still
another alternative embodiments, Orthogonal Signal Correction
("OSC") is employed to aid in the removal of non-glucose spectral
information from the signal. This approach has proven beneficial in
the removal of temperature and time drift related change imprints
on the glucose-related data. Changes in the skin tissue result in
changes in the scattering characteristics of the skin. Removing the
data related to pressure and temperature changes over the course of
the analysis results in a better calibration algorithm that results
in better glucose predictions based on spectral data. Using a
combination approach results in a more improved signal than using
these different approaches individually. For example, the inventors
have found that a combination of Wavelet processing and OSC has
produced excellent results. Additionally, the inventors have found
that the use of Genetic Algorithms in conjunction with OSC has
produced excellent results.
[0049] Similarly, the reference detector 24 detects the beam of
light 23, which is indicative of the light 14 provided to the
optoid, and produces a "reference signal." The reference signal is
processed in a manner similar to the signal produced by the
detector 58.
[0050] Referring now to FIG. 2, a plot of the percentage of light
transmitted through the web versus wavelength (nm) is shown. The
peaks in the plot between from about 1500-1850 nm and about
2100-2400 nm show a high transmission of light 56 though the
tissue. The high absorbency outside these spectral ranges is due,
in part, to absorption by the water contained in the skin. The
glucose in the skin is present, in large part, where the water in
the skin is located. Glucose exhibits unique spectral
characteristics within these two wavelength ranges. More
specifically, 1600-1730 nm and 2100-2380 nm regions.
[0051] The present invention provides further improvement of the
signal-to-noise ratio of the signal-to-noise ratio of the signal
received by the CPU. It will be recalled that the transmission of
light varies as the wavelength of the light is varied by the AOTF
(or other) source, as shown in FIG. 2. It has been found the large
excursions above the base of the curve produce lower
signal-to-noise ratios than would be desired. In some regions of
the spectrum, the peaks are twenty times higher than in other parts
of the spectrum. Thus, in one aspect the improved method of the
invention the height of the peaks above the base line is
effectively reduced in high transmission regions by reducing the
intensity of the light in the appropriate wavelength region to
reduce the height of the peak, with the result that the
signal-to-noise ratio is improved by maximizing the dynamic range
of the instrument in the spectral regions of interest. To
accomplish this result, the CPU 78 is programmed to feed-back to
the AOTF 12 (FIG. 1) the previously determined light transmitted at
each wavelength and to reduce the intensity of the light in the
region where peaks have been found.
[0052] Another improvement related to the feed-back of information
to the AOTF is the modulation of the speed at which the wavelength
range is scanned. Since valuable information is contained in the
peaks of the transmission versus wavelength curve (e.g., FIG. 2).
The scanning rate can be reduced within the peak regions to assure
that the most accurate data is obtained. This also has been found
to improve the signal-to-noise ratio, by averaging or integrating
the data in such regions.
[0053] Further improvement can be obtained by programming the AOTF
to change the amplitude of the radiation in specific regions of the
spectrum determined by measuring the spectrum of a known
composition, for example, a pure glucose sample or glucose in known
fluids. The information obtained from such measurements would help
to characterize the scattering, absorbance, and interference
effects on the spectrum of glucose (or other analyte). The use of a
glucose sample as a filter between the light source and the skin
being tested may also be helpful in determining individual skin
characteristics in sources where the glucose spectrum could not be
programmed in, e.g. broadband light sources.
[0054] In combination, the two improvements just described have
been shown to improve the signal-to-noise by a factor of 10,
compared to the method in which the intensity of the examining
light 14 is constant and the scanning rate is uniform.
[0055] As mentioned above, during the glucose clamping test, in
addition to the transmitted spectral data, samples of blood and ISF
are obtained from the test subject (e.g., the patient subjected to
the test) to determine the subject's actual blood glucose level.
According to one example of the glucose-clamping test, the test is
conducted over an approximately 500 minute duration. The blood and
ISF samples are obtained about every 5 minutes, totaling about 100
samples. These values are then interpolated over the 500 minute
test duration, resulting in about 500 glucose concentration
values.
[0056] The digital spectral signal of the transmitted light is
averaged every minute and stored resulting in about 500 data sets
over the course of the test duration. This data is then analyzed
and processed (described in greater detail below) to build a
calibration algorithm for predicting the actual glucose
concentration level from an examination of the spectral
characteristics of the transmitted light.
[0057] To obtain predicted values, it is necessary to build a
calibration algorithm that predicts the glucose concentration from
the transmitted spectral signal (i.e., the signal produced by the
detector 58). After the spectral signal is filtered by the high and
low frequency filters 74,76, the signal is normalized to correct
for changes in the spectral signal which are the results of
spectral scattering of the light when transmitted through the web
52 and due to the pressure effects of the optoid 34 which is
clamped to the web of skin 52. Failure to correct for these changes
may obscure the spectral information associated with the glucose.
As stated above, less than approximately two percent of the light
input to the web of skin 52 is transmitted to the detector 58.
Accordingly, it is important to account for these types of changes
and irregularities that can lead to errors. The raw signal from the
AOTF spectrometer described above is first normalized to constant
energy, then mean centered to remove constant areas of the
spectrum, creating a normalized, preprocessed series of spectra
that are then checked for outliers by standard methods well known
in the art. Further preprocessing by OSC reduction and wavelets
analysis filtering are done to enhance the glucose signal and to
suppress the water and other background signals. The resulting set
of spectra is then used to build a calibration model by partial
least squares (PLS) regression using Venetian blinds
cross-validation on a portion of the data described above or on all
of the data. Alternative embodiments to the data preparation
described above involve other common methods for reduction or
removal of background signal, including, but not limited to,
first-derivative smoothing, second-derivative smoothing, wavelength
selection by means of genetic algorithms, wavelet processing, and
principal components analysis. Alternative embodiments for the
generation of calibration models can be realized by many different
forms of regression, including principal components regression,
ridge regression or ordinary (inverse) least squares
regression.
[0058] The calibration algorithm to predict the glucose
concentration is then built from the normalized signal. An
orthogonal signal correction process is combined with the time
associated temperature and pressure information to identify the
parts of the spectrum that are associated with these factors and
not strictly related to the changes in the glucose concentration.
This process is used in combination with the correlated data (i.e.,
the invasively determined glucose concentrations of the plasma and
the ISF fluids) to filter out of the spectral data information that
is associated with changes in the other measurements and not with
changes in the glucose. This results in a calibration algorithm
that is much more clearly associated with the changes in the
glucose concentration, and less with artifacts that happen to
correlate to the glucose concentration. Other data improvement
processes include the use of more generic chemometric applications
such as Genetic Algorithms and Wavelet analysis to further refine
the spectral information to the most efficient information. The
Genetic Algorithm and Wavelet analysis are able to select
wavelengths in the spectrum that are specifically related to
glucose and to permit the calibration algorithm to focus on
specific changes in the glucose concentration. The selection is
based on the area of the spectrum where the strongest glucose
related peaks are located, but also the spectral areas related to
the changes in the refractive index of the tissue due to changes in
the tissue concentration. This wavelength selection process results
in retaining the wavelength information that produces the best
calibration algorithm.
[0059] Referring now to FIG. 3, a flow chart depicting a method of
building the glucose calibration algorithm will be described
according to one embodiment of the present invention. Initially, as
described above, a glucose clamping experiment is conducted wherein
spectral information is obtained from the body tissue of at least a
first and a second test subject. This information is stored in a
first data set 82 and a second data set 83. In one embodiment, each
of the first and second data sets 82, 83 includes spectral
information obtain from a plurality of test subjects. Other
information such as body tissue temperature, pressure applied to
the body tissue, and the invasively determined glucose
concentration levels are obtained from each of the test subjects at
predetermined intervals during the glucose clamping test.
[0060] A combined data set, consisting of spectral data from more
than one test subjects (e.g., data from the first and second
spectral data sets 82, 84), is prepared and used to generate a
model useful for prediction of glucose levels for all of the
subjects contributing data. The raw signals, stored in the first
and second data sets 82, 84, from the AOTF spectrometer described
above are first normalized at step 84 to constant energy for data
from each of the test subjects. Portions of the data for each
subject are then combined to form a single, combined spectral set
at step 85, which is then mean centered at step 86 to remove
constant areas of the spectrum, creating a normalized, preprocessed
series of spectra that are then checked for outliers by standard
methods known in the art. Further preprocessing by OSC reduction
and wavelets analysis filtering are done to enhance the glucose
signal and to suppress the water and other background signals. The
resulting set of spectra is then used to build a calibration model
by partial least squares (PLS) regression as step 87 using Venetian
blinds cross-validation on a portion of the data described above or
on all of the data. Alternative embodiments to the data preparation
described above involve other common methods for reduction or
removal of background signal, including, but not limited to,
first-derivative smoothing, second-derivative smoothing, wavelength
selection by means of genetic algorithms, wavelet processing and
principal components analysis. Alternative embodiments for the
generation of calibration models can be realized by many different
forms of regression, including principal components regression,
ridge regression or ordinary (inverse) least squares
regression.
[0061] The PLS model, which was created at step 87, is applied to
the orthogonal signal corrected, normalized first data set at step
89, which results in the glucose calibration algorithm at step 90.
The glucose calibration algorithm 90 is used to predict glucose
concentration based upon spectral information obtained from a test
subject. Put another way, the glucose calibration algorithm is able
to determine the glucose concentration of a test subject based upon
the spectral information (e.g., transmitted or reflected spectral
information) obtained from a test subject. The glucose calibration
algorithm 90 is then applied to the orthogonal signal corrected,
normalized second data set at step 91 for predicting the glucose
contraction values of the test subject(s) of the second spectral
data set 83 at step 92. The glucose concentration values predicted
at step 92 are then compared to the invasively determined glucose
concentration obtained during the glucose clamping test to check
the accuracy of the glucose calibration algorithm at step 93.
[0062] In an alternative embodiment, building the glucose
calibration algorithm also includes applying a Wavelets analysis to
each of the data sets after OSC step 88, which filters the data.
Additionally, in other alternative embodiments, the spectral data
sets 82, 83 include spectral data modeled for glucose concentration
levels which are outside the range of glucose concentration levels
achieved during the glucose clamping test. In one embodiment, the
AOTF spectrometer 12 can be used to create spectral data outside
the ranges achieved during the glucose clamping test.
Reflectance-Based System
[0063] Referring now to FIGS. 4a and 4b, a reflectance-based
non-invasive system 90 for the determination of analytes in body
fluids is illustrated. Briefly, the system 90 inputs near infrared
light into a portion of a patient's skin, such as a forearm, and
records the amount of light reflected from the skin to determine
the patient's glucose level.
[0064] A monochromatic beam of light is input to a bundle 100 of
fiber optic cables. While the bundle 100 of fiber optic cables
depicted in FIG. 5b shows two concentric circles or rows of fiber
optic cables 101, any reasonable number of rows of fiber optic
cable can be used. The monochromatic beam of light is generated in
a manner similar to that described in connection with FIG. 1. An
AOTF spectrometer (not shown) outputs a beam of light 94 having a
resolution of four to ten nanometers ("nm"), which is swept (back
and forth) across a wavelength range of about 2200-4500 nanometers
to the fiber optic cable bundle 100. The fiber optic cable bundle
100 delivers light 94 to an optoid 104. The optoid 104 consists of
the hardware that interfaces with a patient's skin. The optoid 104
includes a plate 106 having a window 108 formed therein. Light 102
is directed through the window 108 onto the patient's skin 110.
According to one embodiment of the present invention, the window
108 is a sapphire window.
[0065] In use, the optoid 104 is brought into contact with a
patient's skin 110 such as the patient's forearm, such that skin
110 rests on the plate 106 and window 108. Light 102 is directed
through the window 108 into the skin 110. The light penetrates the
skin 110 to a depth of about 300 microns and is then reflected from
inside the skin 110. The reflected light 112 is represented by
arrows. The reflected light 112 is directed to a detector 114 via a
sapphire rod 116 disposed within the fiber optic bundle 100. The
reflected light 112 is detected by the detector 114 in a manner
similar to the transmitted light 56 discussed in connection with
FIG. 1.
[0066] According to an alternative embodiment of the
reflectance-based, non-invasive system 90, only a portion of the
fiber optic cables 101 are used to deliver light to the optoid 104,
which varies the path length of the delivered light. For example,
only an inner ring of fiber optic cables 101 is utilized according
to one embodiment and only the outer ring of fiber optic cables 101
are utilized according to another embodiment. Varying the path
length of the delivered light allows the sampling of reflected
light from different depths in the tissue. According to some
embodiments, the various path lengths are used to correct for
individual tissue characteristics such as scattering.
[0067] The optoid 104 of the reflectance-based non-invasive system
90 provides temperature control to the area of skin from which the
reflectance signal is being taken. According to one embodiment of
the present invention, the plates 106 of the optoid include
thermoelectric heaters for heating the skin to approximately
100.degree..+-.0.1.degree. F. Again, heating the skin to uniform
temperature reduces scattering of light, which is a function of
temperature. Additionally, as discussed above, heating the skin
causes the capillaries to expand thus increasing the volume of
blood in the capillaries approximately three hundred percent.
[0068] According to one embodiment of the present invention, an
index matching material 113 is disposed between the skin 110 and
the window 108, for maintaining a constant and matched index for
the light 102 directed into the skin 110 and the light reflected
from the skin 112. The index matching gel reduces large index of
refraction changes that would occur normally between skin and a gap
of air. These large changes result in Fresnel losses that are
especially significant in a reflectance based analysis, which
creates significant changes in the spectral signal. According to
one embodiment of the present invention, the indexing matching
material is a chloro-fluoro-carbon gel. This type of indexing
material has several favorable properties. First, the
chloro-fluoro-carbon gel minimally impacts the spectral signal
directed through the gel. Second, this indexing matching material
has a high fluid temperature point so that it remains in a gel-like
state during the analysis and under test conditions. Third, this
gel exhibits hydrophobic properties so that it seals the sweat
glands so that sweat does not fog-up (i.e., form a liquid vapor on)
the sapphire window 108. And fourth, this type of index matching
material will not be absorbed into the stratum corneum during the
analysis.
[0069] The output of the detector 114 is filtered and processed in
a manner similar to that described in conjunction with the
above-described transmission-based system 10.
[0070] Referring now to FIG. 5, a plot of the absorption of light
input to the skin versus wavelength is shown. As can be seen in
FIG. 5, high absorption is observed in the 1350-1550 nm and the
1850-2050 spectral range.
[0071] The calibration algorithm for the reflectance-based system
is built by applying similar data processing techniques as
discussed in connection with the transmission-based system.
Varying the Applied Light or the Returning Light to Improve
Accuracy
[0072] Once it has been seen how the invention may be employed in
an important application, that is, the non-invasive determination
of the glucose content of body fluid, the variations of the method
may be more readily understood, including their applications where
similar problems are found.
[0073] The proposed variations will be discussed first with
reference to the measurement of glucose in the presence of
substantial amounts of water, which interferes with the measurement
of small amounts of glucose. The absorption of light by glucose and
water affects the returning light, that is the reflected light or
the transmitted light. Since the glucose and water have similar
characteristics it is difficult to separate the absorption due to
glucose from that of water. This is especially a problem when the
analyte, glucose, is present in much smaller amounts relative to
water. In the present invention, either the light source is
manipulated by the central processing unit or the returning light
is examined after detection in a related manner.
[0074] Consider the case in which an AOTF is used as a source of
light. While it is easier to appreciate the variations of the
method when they are applied to the use of an AOTF as the light
source, it should be understood that other light sources may be
used in instruments that measure analytes by means of their
absorption of light within certain characteristic ranges. In the
simplest case, the sample is exposed to light having a
predetermined range of wavelengths. That range is swept through in
sequence with equal intensity applied at each wavelength. Such a
process produces the results shown in FIGS. 2 and 5. Since it is
known that glucose (or another analyte) has certain
characteristics, that is, it absorbs light at certain wavelengths
more than others, the absorption of light does not clearly
distinguish glucose in the presence of water without further
manipulation of the data, as has been discussed earlier. The
present invention also includes new processing steps that further
improve the accuracy of the results, since the light absorbed is
more easily characterized. The new processing steps are discussed
as applied to altering the light produced by an AOTF, but may be
applied similarly to processing of light returning from the sample
to the detector.
[0075] Once the results of a scan of the suitable range of light
wavelengths with uniform intensity is obtained, the central
processing unit is programmed to repeat the scan, but with the
intensity at each wavelength adjusted during the repeat scan so
that the returning light has equal intensity at each of the
wavelengths examined. Such a procedure has the effect of
suppressing the relative absorption of water so that the
signal-to-noise ratio is improved, because the detector becomes
more sensitive to the presence of glucose at its characteristic
wavelengths.
[0076] A further improvement may be obtained by scanning the
desired range of wavelengths non-uniformly, that is, dwelling for
longer periods at wavelengths identified as containing more useful
information about the glucose, relative to water or to other
interfering substances. Then, the returning light can be given more
importance in the mathematical analysis of the data.
[0077] Another variation of the scanning process examines only
those wavelengths where it has been found that the signal-to-noise
ratio is the highest, that is, where the interference of water and
other substances is the least. The effect of absorption by glucose
would be likely to be more clearly seen and therefore the accuracy
of the results would be expected to be improved.
[0078] A related method would examine only certain regions in which
it has been found that information on glucose is more readily
distinguished from water or other interfering substances. For
example, the absorption of light by glucose and water broadly
speaking occurs in similar regions. However, the response varies
with temperature and it is therefore feasible to distinguish
between glucose and water in certain regions where their difference
in absorption of light is more easily seen as the temperature of
the sample is varied.
[0079] The light source may also be supplied with information that
corrects for changes in the analyte-related spectrum caused by the
sample, the delivery and collection methods (e.g., fibers or
lenses) and detector distortions. If changes to the returning light
related to the associated equipment and the sample itself can be
corrected for, determining the amount of the analyte can be done
with improved accuracy.
[0080] For various reasons, the response of the analyte may not be
as linear as would be expected. Therefore, the light source may
contain concentration-related spectra that correct for the
non-linearly of response.
[0081] It will be evident to those skilled in the art that some of
the methods just discussed may be applied to the detection and
analysis of data contained in light returning from the sample.
Furthermore, any one or up to all of the improved methods may be
applied in order to improve the signal related to the analyte and
thus to increase the accuracy of the analysis. Preferably, a
sequence of these methods would be applied to refine the
determination of the analyte to improve the accuracy of the
results.
[0082] While the present invention has been described with
reference to one or more particular embodiments, those skilled in
the art will recognize that many changes may be made thereto. Each
of these embodiments and obvious variations thereof is contemplated
as falling within the scope of the invention.
Alternative Embodiment A
[0083] A system for determining the concentration of an analyte in
a fluid sample, the system comprising:
[0084] a light source delivering light within a predetermined
wavelength range;
[0085] a detector adapted to receive spectral information
corresponding to light returned from said fluid and to convert the
received spectral information into an electrical signal indicative
of the received spectral information; and
[0086] a central processing unit adapted to compare the electrical
signal to an algorithm built upon correlation with the analyte in
the body fluid, the algorithm adapted to convert the received
spectral information into the concentration of said analyte in said
fluid, the central processing unit controlling the light source and
varying the intensity and timing of the delivery of said light
within said predetermined wavelength range to improve the accuracy
of conversion of the received spectral information into
concentration of said analyte in said fluid.
Alternative Embodiment B
[0087] The system of Alternative Embodiment A wherein said light
source is a series of beams of monochromatic light that scan across
the predetermined wavelength range.
Alternative Embodiment C
[0088] The system of Alternative Embodiment B further comprising a
reference detector adapted to receive a portion of said series of
beams of monochromatic light and to convert the received light into
a reference electrical signal.
Alternative Embodiment D
[0089] The system of Alternative Embodiment C wherein said light
source is adapted to modulate the monochromatic beams of light, and
further comprising at least one lock-in amplifier electrically for
demodulating the reference electrical signal and for demodulating
the electrical signal indicative of the received spectral
information.
Alternative Embodiment E
[0090] The system of Alternative Embodiment B wherein said
monochromatic light is delivered to said fluid sample sequentially
across a predetermined wavelength range.
Alternative Embodiment F
[0091] The system of Alternative Embodiment E wherein the intensity
of said monochromatic light is uniform over said predetermined
wavelength range.
Alternative Embodiment G
[0092] The system of Alternative Embodiment E wherein the intensity
of said monochromatic light is varied across said predetermined
wavelength range to provide spectral information received from said
sample having uniform intensity across said predetermined
wavelength range.
Alternative Embodiment H
[0093] The system of Alternative Embodiment E wherein said
monochromatic light is delivered to said sample for predetermined
periods of time at predetermined wavelengths.
Alternative Embodiment I
[0094] The system of Alternative Embodiment H wherein said
monochromatic light is delivered to said sample at predetermined
wavelengths where the signal-to-noise ratio is the greatest.
Alternative Embodiment J
[0095] The system of Alternative Embodiment H wherein said
monochromatic light is delivered to said sample at predetermined
wavelengths where said analyte is more readily distinguished from
interfering substances.
Alternative Embodiment K
[0096] The system of Alternative Embodiment A wherein said light
source delivers to said sample predetermined wavelengths of light
at predetermined intensities and said spectral information returned
from said sample is processed to provide spectral information
having uniform intensity at said predetermined wavelengths.
Alternative Embodiment L
[0097] The system of Alternative Embodiment A wherein said light
source delivers to said sample predetermined wavelengths of light
at predetermined intensities and said spectral information returned
from said sample is processed to provide spectral information at
predetermined wavelengths where the signal-to-noise ratio is the
greatest.
Alternative Embodiment M
[0098] The system of Alternative Embodiment A wherein said light
source delivers to said sample predetermined wavelengths of light
at predetermined intensities and said spectral information returned
from said sample is processed to provide spectral information at
wavelengths where said analyte is more readily distinguished from
interfering substances.
Alternative Embodiment N
[0099] The system of Alternative Embodiment A wherein said light
source contains information that is used to correct for the effect
on the light spectra of the sample, light delivery and collection
systems, and detector.
Alternative Embodiment O
[0100] The system of Alternative Embodiment A wherein said light
source contains information that corrects for changes in the
analyte-related spectrum by the sample, light delivery and
collection methods, and detector distortions.
Alternative Embodiment P
[0101] The system of Alternative Embodiment A wherein said light
source contains concentration-related spectra that correct for
non-linear responses of the analyte.
Alternative Process Q
[0102] The method for determining the concentration of an analyte
in a fluid sample, the method comprising the acts of:
[0103] delivering light within a predetermined wavelength range
from a light source;
[0104] receiving spectral information corresponding to light
returned from said fluid;
[0105] converting the received spectral information into an
electrical signal indicative of the received spectral
information;
[0106] comparing the electrical signal to an algorithm built upon
correlation with the analyte in the body fluid; and
[0107] converting the received spectral information into the
concentration of said analyte in said fluid via a central
processing unit,
[0108] wherein the central processing unit controls the light
source and varies the intensity and timing of the delivery of said
light within said predetermined wavelength range to improve the
accuracy of conversion of the received spectral information into
concentration of said analyte in said fluid.
Alternative Embodiment R
[0109] A system for determining the concentration of an analyte in
body tissue fluid, the system comprising:
[0110] an infrared light source delivering substantially
monochromatic light sequentially across a predetermined wavelength
range;
[0111] a body tissue interface adapted to contact body tissue and
to deliver light from said infrared light source to the contacted
body tissue;
[0112] a detector adapted to receive spectral information
corresponding to infrared light transmitted through the contacted
body tissue and to convert the received spectral information into
an electrical signal indicative of the received spectral
information; and
[0113] a central processing unit adapted to compare the electrical
signal to an algorithm built upon correlation with the analyte in
the body fluid, the algorithm adapted to convert the received
spectral information into the concentration of the analyte in the
body fluid, said central processing unit controlling said infrared
light source and varying the intensity and timing of the delivery
of said monochromatic light within the predetermined wavelength
range to improve the accuracy of conversion of the received
spectral information into concentration of said analyte in said
fluid.
Alternative Embodiment S
[0114] The system of Alternative Embodiment R wherein said infrared
light source is an acoustic optical tunable filter (AOTF).
Alternative Embodiment T
[0115] The system of Alternative Embodiment S wherein said
wavelength range is from about 1400 nanometers to about 2500
nanometers.
Alternative Embodiment U
[0116] The system of Alternative Embodiment R wherein said body
fluid is extracellular fluid and said analyte is glucose.
Alternative Embodiment V
[0117] The system of Alternative Embodiment U wherein said infrared
light source is modulated to correspond to a spectrum obtained by
interaction of the infrared light with a pure glucose sample.
Alternative Embodiment W
[0118] The system of Alternative Embodiment U wherein the intensity
of said monochromatic light is uniform over said predetermined
wavelength range.
Alternative Embodiment X
[0119] The system of Alternative Embodiment U wherein the intensity
of said monochromatic light is varied across said predetermined
wavelength range to provide spectral information received from said
sample having uniform intensity across said predetermined
wavelength range.
Alternative Embodiment Y
[0120] The system of Alternative Embodiment U wherein said
monochromatic light is delivered to said sample for predetermined
periods of time at predetermined wavelengths.
Alternative Embodiment Z
[0121] The system of Alternative Embodiment Y wherein said
monochromatic light is delivered to said sample at predetermined
wavelengths where the signal-to-noise ratio is the greatest.
Alternative Embodiment AA
[0122] The system of Alternative Embodiment Y wherein said
monochromatic light is delivered to said sample at predetermined
wavelengths where said analyte is more readily distinguished from
interfering substances.
Alternative Embodiment BB
[0123] The system of Alternative Embodiment U wherein said
monochromatic light delivers to said sample predetermined
wavelengths of light at predetermined intensities and spectral
information returned from said sample is processed to provide
spectral information having uniform intensity at said predetermined
wavelengths.
Alternative Embodiment CC
[0124] The system of Alternative Embodiment U wherein said
monochromatic light delivers to said sample predetermined
wavelengths of light at predetermined intensities and said spectral
information returned from said sample is processed to provide
spectral information at predetermined wavelengths where the
signal-to-noise ratio is the greatest.
Alternative Embodiment DD
[0125] The system of Alternative Embodiment U wherein said
monochromatic light delivers to said sample predetermined
wavelengths of light at predetermined intensities and said spectral
information returned from said sample is processed to provide
spectral information at wavelengths where said analyte is more
readily distinguished from interfering substances.
Alternative Embodiment EE
[0126] The system of Alternative Embodiment U wherein said
monochromatic light contains information that is used to correct
for the effect on the light spectra of the sample, light delivery
and collections systems, and detector.
Alternative Embodiment FF
[0127] The system of Alternative Embodiment U wherein said light
source contains information that corrects for changes in the
analyte-related spectrum by the sample, light delivery and
collection methods, and detector distortions.
Alternative Embodiment GG
[0128] The system of Alternative Embodiment U wherein said light
source contains concentration-related spectra that correct for
non-linear responses of the analyte.
Alternative Process HH
[0129] A method for determining the concentration of an analyte in
body tissue fluid, the method comprising the acts of:
[0130] delivering substantially monochromatic light from an
infrared light source sequentially across a predetermined
wavelength range;
[0131] contacting body tissue with a body tissue interface;
[0132] delivering light from said infrared light source to the
contacted body tissue;
[0133] receiving spectral information corresponding to infrared
light transmitted through the contacted body tissue;
[0134] converting the received spectral information into an
electrical signal indicative of the received spectral
information;
[0135] comparing the electrical signal to an algorithm built upon
correlation with the analyte in the body fluid using a central
processing unit; and
[0136] converting the received spectral information into the
concentration of the analyte in the body tissue fluid using the
algorithm,
[0137] wherein the central processing unit controls said infrared
light source and varies the intensity and timing of the delivery of
said monochromatic light within the predetermined wavelength range
to improve the accuracy of conversion of the received spectral
information into concentration of said analyte in said fluid.
Alternative Embodiment II
[0138] A system for determining the concentration of an analyte in
body tissue fluid, the system comprising:
[0139] an infrared light source delivering substantially
monochromatic light sequentially across a predetermined wavelength
range;
[0140] a body tissue interface adapted to contact body tissue and
to deliver light from said infrared light source to the contacted
body tissue;
[0141] an index matching medium disposed between the body tissue
interface and said body tissue, wherein the infrared light
delivered to said body tissue and reflected by the body tissue
passes through said index matching medium;
[0142] a detector adapted to receive light reflected from the body
fluid and to convert the received reflected light into an
electrical signal indicative of the received reflected light;
and
[0143] a central processing unit adapted to compare the electrical
signal to an algorithm built upon correlation with the analyte in
the body fluids, the algorithm converting the received spectral
information into the concentration of the analyte in said body
fluid, said central processing unit controlling said infrared light
source and varying the intensity and timing of the delivery of said
monochromatic light with the predetermined wavelength range to
improve the accuracy of conversion of the received spectral
information into concentration of said analyte in said fluid.
Alternative Embodiment JJ
[0144] The system of Alternative Embodiment II wherein said
infrared light sources is an optical tunable filter (AOTF).
Alternative Embodiment KK
[0145] The system of Alternative Embodiment JJ wherein the infrared
light has a wavelength ranging between approximately 1400
nanometers and approximately 2500 nanometers.
Alternative Embodiment LL
[0146] The system of Alternative Embodiment II wherein said body
fluid is extracellular fluid and said analyte is glucose.
Alternative Embodiment MM
[0147] The system of Alternative Embodiment LL wherein said
monochromatic infrared light is modulated to correspond to a
spectrum obtained by interaction of the light with a pure glucose
sample.
Alternative Embodiment NN
[0148] The system of Alternative Embodiment LL wherein the
intensity of said monochromatic light is uniform over said
predetermined wavelength range.
Alternative Embodiment OO
[0149] The system of Alternative Embodiment LL wherein the
intensity of said monochromatic light is varied across said
predetermined wavelength range to provide spectral information
received from said sample having uniform intensity across said
predetermined wavelength range.
Alternative Embodiment PP
[0150] The system of Alternative Embodiment LL wherein said
monochromatic light is delivered to said sample for predetermined
periods of time at predetermined wavelengths.
Alternative Embodiment QQ
[0151] The system of Alternative Embodiment PP wherein said
monochromatic light is delivered to said sample at predetermined
wavelengths where the signal-to-noise ratio is the greatest.
Alternative Embodiment RR
[0152] The system of Alternative Embodiment PP wherein said
monochromatic light is delivered to said sample at predetermined
wavelengths where said analyte is more readily distinguished from
interfering substances.
Alternative Embodiment SS
[0153] The system of Alternative Embodiment LL wherein said
monochromatic light delivers to said sample predetermined
wavelengths of light at predetermined intensities and spectral
information returned from said sample is processed to provide
spectral information having uniform intensity at said predetermined
wavelengths.
Alternative Embodiment TT
[0154] The system of Alternative Embodiment LL wherein said
monochromatic light delivers to said sample predetermined
wavelengths of light at predetermined intensities and said spectral
information returned from said sample is processed to provide
spectral information at predetermined wavelengths where the
signal-to-noise ratio is the greatest.
Alternative Embodiment UU
[0155] The system of Alternative Embodiment LL wherein said
monochromatic light delivers to said sample predetermined
wavelengths of light at predetermined intensities and said spectral
information returned from said sample is processed to provide
spectral information at wavelengths where said analyte is more
readily distinguished from interfering substances.
Alternative Embodiment VV
[0156] The system of Alternative Embodiment LL wherein said
monochromatic light contains information that is used to correct
for the effect on the light spectra of the sample, light delivery
and collections systems and detector distortions.
Alternative Embodiment WW
[0157] The system of Alternative Embodiment LL wherein said light
source contains information that corrects for changes in the
analyte-related spectrum by the sample, light delivery and
collection methods, and detector distortions.
Alternative Embodiment XX
[0158] The system of Alternative Embodiment LL wherein said light
source contains concentration-related spectra that correct for
non-linear responses of the analyte.
Alternative Process YY
[0159] A method for determining the concentration of an analyte in
body tissue fluid, the method comprising the acts of:
[0160] delivering substantially monochromatic light using an
infrared light source sequentially across a predetermined
wavelength range;
[0161] contacting body tissue using a body tissue interface;
[0162] delivering light from said infrared light source to the
contacted body tissue;
[0163] placing an index matching medium between the body tissue
interface and said body tissue, wherein the infrared light
delivered to said body tissue and reflected by the body tissue
passes through said index matching medium;
[0164] receiving light reflected from the body fluid;
[0165] converting the received reflected light into an electrical
signal indicative of the received reflected light;
[0166] comparing the electrical signal to an algorithm built upon
correlation with the analyte in the body fluids via a central
processing unit; and
[0167] converting the received spectral information into the
concentration of the analyte in said body fluid,
[0168] wherein the central processing unit controls said infrared
light source and varies the intensity and timing of the delivery of
said monochromatic light with the predetermined wavelength range to
improve the accuracy of conversion of the received spectral
information into concentration of said analyte in said fluid.
[0169] While the invention is susceptible to various modifications
and alternative forms, specific embodiments are shown by way of
example in the drawings and described in detail. It should be
understood, however, that it is not intended to limit the invention
to the particular forms disclosed, but on the contrary, the
intention is to cover all modifications, equivalents, and
alternatives falling within the spirit and scope of the invention
as defined by the appended claims.
* * * * *